Ophthalmic surgical device for capsulotomy

ABSTRACT

A surgical device and procedure are provided for performing microsurgery, including a capsulotomy of a lens capsule of an eye. The device has an elastically deformable cutting element mounted within an elastomeric suction cup. The suction cup is attached to an arm for manipulating the device. The device can be inserted into the anterior chamber of the eye, through a corneal incision, to cut a piece from the anterior portion of the lens capsule of the eye. The device is secured against the lens capsule using suction applied by one or more suction elements. The device is then removed from the eye, with the cut piece of membrane retained within the device by suction.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.15/001,128, filed on Jan. 19, 2016, which is a continuation of U.S.patent application Ser. No. 14/106,603, filed on Dec. 13, 2013, now U.S.Pat. No. 9,271,868, which is a continuation of U.S. patent applicationSer. No. 12/990,163, filed on Dec. 10, 2010, now U.S. Pat. No.8,702,698, which is a national phase application of PCT/US2009/043828,filed on May 13, 2009, which claims the benefit of U.S. ProvisionalApplication No. 61/127,700, filed May 15, 2008, entitled “OphthalmicSurgical Device for Capsulotomy,” and of U.S. Provisional ApplicationNo. 61/201,465, filed Dec. 11, 2008, entitled “Ophthalmic SurgicalDevice for Capsulotomy,” the entire disclosures of which are herebyincorporated by reference herein, including any appendices orattachments thereof, in their entirety for all purposes.

BACKGROUND

This invention pertains in general to microsurgery of tissue, and morespecifically to procedures and devices for creating precise openings intissue of a desired diameter and shape. For example, the procedures anddevices can be used in ophthalmic surgery of the anterior lens capsulemembrane of an eye.

Lens cataract is the leading cause of blindness worldwide and surgicaltreatment by cataract removal is the treatment of choice. A cataract isa clouding that develops in the lens of the eye or in its envelope. Thecreation of areas of opacity in the lens obstructs the passage of light.The lens of the eye is supposed to be transparent. If the lens developsopaque areas, as in a cataract, the lens must be surgically removed. Ifno lens is present in the eye, heavy corrective glasses are required tofocus an image on the retina. The lens, however, can be replaced with anartificial interocular lens (IOL) to provide better vision aftercataract removal.

The removal of the lens for replacement with an IOL is a surgicalprocedure that requires substantial precision. The lens is completelyenclosed by a membrane called the lens capsule, so the surgeon mustfirst cut through the capsule to access the lens. It is important to cutthe capsule in just the right way. If the lens capsule has been cutcorrectly, and not damaged during the cataract removal, then it can beused to hold an IOL. The implantation of an IOL requires the creation ofan opening in the lens capsule that is precisely centered, sized, andshaped for implant stability and for optimal IOL function. The matchingof the lens capsule opening size to the peripheral margins of the IOL iscritical. The goal of the surgeon is to create a perfectly circular(e.g., 5.5+/−0.1 mm diameter) hole in the capsule, centered exactly onthe optical axis of the eye, with no tears or defects in the edge of thehole. Tears or defects on the edge of the hole make the capsule veryweak and vulnerable to losing the ability to hold the IOL properly.Different IOL designs may require a different diameter for the hole(e.g., ranging from 4.5+/−0.1 mm to 5.75+/−0.1 mm), but whatever theprescribed diameter is, the accuracy of the surgeon in actuallyachieving it is very important for proper outcome of the cataractsurgery.

Creating an opening in the lens capsule with this required level ofprecision is a difficult task for a surgeon controlling and guidingconventional hand-held cutting instruments and attempting to trace aprecise circular route on the lens capsule. The present state of the artfor performing a capsulotomy (the creation of an opening in the lenscapsule) is for the surgeon to manually create a small tear in theanterior region of the lens capsule. With great caution, the surgeonthen uses a small needle-like cystotome and/or tweezers to try to extendthe edge of the tear so as to follow a circular path of the specifieddiameter and centered on the optic axis of the eye. In practice it oftenhappens that the hole does not end up circular, or the correct diameter,or centered on the optic axis. There can also be radial tears in theedge of the hole that greatly weaken the capsule. As a result of any ofthese errors, the capsule may not be able to hold the IOL properly.

A number of devices have attempted to address the capsulotomy problem,but these devices still raise a number of challenging problems.Electrocautery devices have been used in the past to try to burn thelens capsule tissue and/or weaken it enough so that it is possible tothen go in with hand-held tweezers and more easily tear out the circularpatch of membrane. However, these devices often require massive heatingelements to heat up the tissue, and so are rather bulky devices for usein performing delicate capsulotomy procedures on small tissuestructures. Further, applying heat to a patient's eye to burn tissue isgenerally a risky procedure. The heat is often applied for a long time,lengthening the procedure and putting the patient at risk. With theseelectrocautery instruments, it is necessary to put a great deal ofenergy into the eye, thereby risking damage to tissue near to thecapsule. In addition, the electrocautery devices do not complete thecapsulotomy, but instead inconveniently leave the partially burnt orweakened capsule behind, thus requiring yet another step and anothertool (e.g., tweezers) to fish out the capsule piece for removal. Thisadds further time to the procedure and puts the patient at risk byrequiring more than one tool to be placed in proximity to the patient'seye.

Mechanical knife devices have also been used for performingcapsulotomies. These devices are used to try to cut the capsule membranewith a small knife, applying the same cutting mechanism as would be usedwith a large handheld knife. The problem with cutting tissue on themicroscale level with a knife is that the volume of tissue is so small,it has microscopic stiffness. Therefore, the tissue must be stretchedrelatively far to build up enough stress to provide the force againstthe cutting edge of the knife (no matter how sharp) for cutting tooccur. The scale of stretching is up to a millimeter, and thisdistortion is greater than the desired precision (e.g., less than 0.1mm), so it is not a satisfactory mechanism. Also, in practice, severalpasses with the knife may have to be made over the same cutting locationto actually cut all the way through the membrane. Further, precisemicrocuts are often not easily reproducible with these microknives.

Given the drawbacks of existing treatment devices/procedures for lenscapsule surgery, improved techniques and devices for performingmicrosurgery are needed.

SUMMARY

Embodiments of the invention provide microsurgery techniques and devicesfor performing, for example, lens capsule surgery. Embodiments of theinvention automate the capsulotomy step of lens capsule surgery, such asfor a cataract operation, while the other steps of the cataractoperation are not impacted and so can be performed in the usual manner.In various embodiments, an opening is created in the lens capsule of theeye using a device that includes a cutting instrument and a mechanismfor creating the cut along a desired cutting path (e.g., a circle). Insome embodiments, the surgeon centers the device over the lens, pressesa button, and within 10 seconds or less the device can be removed fromthe eye along with the circular patch of capsular membrane that it hascut out. The microsurgical device removes many of the manual stepsperformed by surgeons in previous techniques, which in turn facilitatesmore precise cutting of the lens capsule. This allows for surgicalprocedures that are relatively short in duration compared to previoussurgical procedures, and it allows those procedures to be accomplishedreliably with average surgical skill. The microsurgical device alsoaddresses many of the problems described above with automated devices,including issues with bulky devices, lengthy procedures, risky burningof tissue, lengthy time periods for application of heat, multistepprocedures involving multiple tools, microscopic stiffness problems withcutting tissue, among others.

Embodiments of the invention include devices and methods for performinga capsulotomy. In one embodiment, the device includes a suction cuphaving a roof and an underside, the underside having inner and outerchambers, an arm attached to the suction cup for moving the device intocontact with the lens capsule, and one or more suction elementsconnected to the suction cup. The elements can provide suction to thechambers to secure the suction cup to the lens capsule of the eye. Theelements can also be configured for providing suction (e.g., to theinner chamber) to retain the severed portion during removal of thedevice. A cutting element mounted to or mounted in relation to thesuction cup (e.g., mounted to the underside of the suction cup orotherwise mounted to that the cutting element is positioned to face thetissue) is configured to cut a portion of tissue (e.g., a circularportion) of the lens capsule pulled into the suction cup by the suctionprovided by the suction elements.

In operation, the surgeon moves a capsulotomy device (e.g., the devicedescribed above) to a position proximate to the lens capsule of the eye.Suction can be applied to the suction cup for securing the cup to thelens capsule (e.g., by pulling tissue into the suction cup), and forpulling tissue of the lens capsule into the suction cup against acutting element mounted to the suction cup. The procedure furtherincludes cutting a portion of the tissue (e.g., a circular portion) ofthe lens capsule pulled into the suction cup. The suction can then bereduced for releasing the suction cup from the tissue, and the deviceremoved from the eye.

In another embodiment of the method involving a capsulotomy device(e.g., the device described above), the device is again moved intocontact with the lens capsule, and suction is applied to the suction cupto secure the suction cup against the lens capsule. A circular portionof the tissue of the lens capsule is cut with the cutting element.Suction is then reduced (e.g., to the inner chamber) for releasing thesuction cup and retaining the circular portion severed in the suctioncup. The device is then removed from the eye and the portion of tissuesevered retained by suction within the suction cup (e.g., the innerchamber).

In other embodiments of the invention for performing microsurgery oftissue (e.g., including tissue other than the lens capsule), the deviceagain includes a suction cup with inner and outer chambers, an armattached to the suction cup for moving the device into contact with thetissue, and one or more suction elements connected to the suction cup.The elements can provide suction to the chambers to secure the suctioncup against the tissue. A cutting element is located within the outerchamber and mounted to the suction cup (e.g., around the periphery of orwithin an annular region of the suction cup). The cutting element isconfigured to cut free a portion of the tissue pulled by suction intothe suction cup. The suction elements can release the suction to releasethe suction cup from the tissue while providing suction to the innerchamber for retaining the severed tissue portion during removal of thedevice.

In operation, the surgeon moves a microsurgery device (e.g., themicrosurgery device above) to a position proximate to the tissue, andapplies suction to the suction cup for pulling an area of the tissueinto the suction cup to secure the suction cup against the tissue. Thesuction also pulls the tissue into position for cutting. The methodfurther includes cutting free a portion of the tissue pulled into thesuction cup against a cutting element. The suction is then released fromone of the chambers (e.g., the outer chamber) of the suction cup torelease the cup from the tissue. The suction is however maintained inanother of the chambers (e.g., the inner chamber) for holding theportion severed in the suction cup. The surgeon removes the microsurgerydevice from the tissue, along with the portion of the tissue severed,which is retained in the device.

These techniques enable a surgeon to perform minimally invasivemicrosurgery on tissue, such as the lens capsule, which results inrelatively low collateral damage to neighboring tissues as compared withprevious treatment techniques. The techniques described herein alsoprovide a high level of control of the positioning and orientation ofthe cutting instrument for precise location and sizing of the incisionin the lens capsule.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagram of the microsurgery/capsulotomy device, according toan embodiment of the invention.

FIG. 2 is a cross-sectional view of the microsurgery/capsulotomy device,according to an embodiment of the invention.

FIG. 3a illustrates the microsurgery/capsulotomy device in use in theanterior chamber of the eye, according to an embodiment of theinvention.

FIG. 3b illustrates a suction cup withdrawn into an insertion tube ofthe device, according to an embodiment of the invention.

FIGS. 4-9 illustrate schematically the steps involved in the use of thedevice, according to an embodiment of the invention.

FIGS. 10-11 are cross-sectional views of an overetched heating elementwith insulated sides in the device, according to an embodiment of theinvention.

FIG. 12 is a cross-sectional view of a heating element with a deepcavity, according to an embodiment of the invention.

FIG. 13 is an illustration of a side cutting geometry, according to anembodiment of the invention.

FIG. 14 is an illustration of the device after a side cut has beencompleted, according to an embodiment of the invention.

FIG. 15 is an exploded view of the device components, according to anembodiment of the invention.

FIG. 16 is a close-up view of a heating element and its support ring,according to an embodiment of the invention.

FIG. 17 is an illustration of an inflatable/collapsible suction cupdesign with the web and skin structure, according to an embodiment ofthe invention.

FIG. 18 is an illustration of a meltable wax insert to mold hollowspaces in the web and skin structure, according to an embodiment of theinvention.

FIG. 19 is an illustration of an inflatable/collapsible skin structureto be filled with open-cell foam, according to an embodiment of theinvention.

FIG. 20 is an illustration of the geometry for the inflatable structurewith minimum material, according to an embodiment of the invention.

FIG. 21 is an illustration of a toothed ring for mechanical cutting,according to an embodiment of the invention.

FIG. 22 is a close-up view of the sharp microteeth of the device,according to an embodiment of the invention.

FIG. 23 is an illustration of an electromechanical cutting elementhaving a single tooth, according to an embodiment of the invention.

FIG. 24 is a close-up view of the electrical connections to theelectrical cutting element, according to an embodiment of the invention.

FIG. 25 is a rear view of the microsurgery/capsulotomy device with adisposable unit, according to an embodiment of the invention.

FIG. 26 is a side view of the internal components of the device with thedisposable unit, according to an embodiment of the invention.

FIG. 27 is a top view of the device with the disposable unit, accordingto an embodiment of the invention.

FIG. 28 is a side view of the device with the disposable unit attachedto the reusable handpiece, according to an embodiment of the invention.

FIG. 29a is a flow chart illustrating the microsurgery/capsulotomyprocedure, according to an embodiment of the invention.

FIG. 29b is a continuation of the flow chart of FIG. 29a illustratingthe microsurgery/capsulotomy procedure, according to an embodiment ofthe invention.

The figures depict an embodiment of the present invention for purposesof illustration only. One skilled in the art will readily recognize fromthe following description that alternative embodiments of the structuresand methods illustrated herein may be employed without departing fromthe principles of the invention described herein.

DETAILED DESCRIPTION Microsurgery/Capsulotomy Device

Embodiments of the invention are described herein in the context of alens capsule surgery in which a portion of the anterior surface of alens capsule is cut. This technique may be used for performing atreatment for cataracts in which all or a portion of a lens locatedwithin the lens capsule is removed from the eye. The procedure may alsobe used to create an access hole in the lens capsule through which toimplant an artificial lens (e.g., an intraocular lens, or IOL) withinthe lens capsule. Moreover, the techniques and devices described hereinmay be useful tools for performing other medical procedures (such ascorneal surgeries or surgeries involving tissue other than that in theeye), which may or may not currently exist.

FIG. 1 is a top perspective view of the microsurgery or capsulotomydevice, and FIG. 2 is a cross-sectional view of the device, according toan embodiment of the invention. The Figures illustrate that the device(50) has a suction cup (67) and an arm or stem (62). The suction cup(67) has a roof (51) and an underside (8). The underside includes aninner chamber (58) and outer chamber (57). The arm/stem (62) is attachedto the suction cup for moving the device into contact with tissue (e.g.,the lens capsule). The roof (51) of the inner chamber (58) can becorrugated in some embodiments, such as is shown in FIG. 1, to make itmore stretchable to deform as needed to enter the insertion tube(illustrated as item number 4 in FIGS. 3a and 3b ).

In some embodiments of the device (50), the suction cup (67) iscollapsible to a small cross section so that it can be inserted througha corneal incision (e.g., an incision of less than 3.0 mm in length).After insertion into the anterior chamber of the eye, the suction cup(67) is designed to rapidly return to its circular shape. The suctioncup (67) can be made of an elastomeric material such as silicone orpolyurethane (e.g., made by casting or by injection molding), thoughother materials can be used as well. The thinner the walls are, thestiffer (higher durometer) the material can be. The size range for thesuction cup would commonly range from about 4.5 mm to about 7 mm indiameter, while the height would commonly range from about 0.5 mm toabout 1.5 mm. However, other suction cup sizes and designs are possible.Particularly for surgery performed outside of the eye (e.g., on otherparts of the body), the suction cup and overall device size ranges canvary to match the surgical procedure being conducted. After insertioninto the anterior chamber of the eye, the device is designed to rapidlyreturn to its circular shape.

There are two types of suction cups (67) that are commonly used with thedevice (50): solid and inflatable. The solid construction is simpler tomake, but the inflatable construction allows passage through a smallerincision, and also develops an internal pressure that can restore thecircular shape of the suction cup and cutting element more rapidly. Ahighly viscous material is typically injected into the eye duringsurgery to keep the anterior chamber from collapsing due to leakagethrough the corneal incision, so the suction cup (67) should be designedto move through this material as it recovers its prior shape. After thecapsule is cut, the suction cup (67) can be collapsed again to a smallercross section for removal through the corneal incision. In someembodiments, even though the suction cup (67) is collapsible, it hasenough stiffness to be maneuvered to the surgery site, unlike many otherdevices that require a rod or other element for maneuvering the deviceinto position. For example, the inflatable designs are made relativelystiff by internal pressure. The solid wall of the non-inflatable designsis stiff enough by virtue of having a thicker wall cross section and/orusing a higher durometer (stiffer) elastomeric material.

The cutting element (60), which is visible in the cross-sectional viewof FIG. 2, is mounted to the suction cup (67). In this embodiment, thecutting element (60) is mounted to the underside of the suction cup (67)within the outer chamber (57), between walls (61) and (59) of the outerchamber (57). However, it can be mounted elsewhere in or on the suctioncup (67), or mounted in relation to the suction cup (67) so that thecutting element (60) is positioned to face the tissue to be cut. Thecutting element (60) is configured to cut a portion of tissue (e.g., ofthe lens capsule). In the embodiments of FIGS. 1 and 2, the cuttingelement (60) is a circular cutting element mounted around the peripheryof the underside (8) of the suction cup (67). However, the cuttingelement (60) can take other shapes (e.g., elliptical, square,rectangular, irregular, and other shapes) for different types ofsurgical procedures where a differently-shaped incision in the tissue isdesired. Similarly, the suction cup (67) can take on other shapes, aswell. The cutting element of the FIG. 2 embodiment is a circular ringhaving a diameter that produces a desired hole or opening in the tissue.

There are at least three different types of cutting elements (50) thatcan be used with the embodiments of device (50): electrical, mechanical,and combined electro-mechanical, though other designs could be used, aswell. The electrical cutting element functions as a resistor. A veryshort electrical pulse quickly heats up the element (e.g., to greaterthan 500° C., such as 600° C., 700° C., 800° C., 900° C., 1000° C.,1200° C., 1500° C., and so forth). In some embodiments, the heatingprocess lasts for a few microseconds (e.g., 10 microseconds or less),though heating times can differ in other embodiments (e.g., 1microsecond, 5 microseconds, 10 microseconds, 20 microseconds, 1millisecond, 5 milliseconds, etc.). The duration of the electricaldischarge is too short for heat to travel more than a few microns byconduction from the cutting element (60), so for a few microseconds thethin layer of water that is trapped between the capsule and the cuttingelement (60) absorbs the energy of the discharge and forms steam. Thesteam expands and increases the tensile stress in the capsule enough totear it.

Since the electrical current is applied for only a few microseconds,tissue is not burned as it is with electrocautery instruments used inthe past for performing capsulotomies. Due to this, the device (50)avoids the risks associated with burning tissue in a patient's eye, withpossible collateral damage to nearby tissue, with lengthy application ofheat, and other problems. The energy of the electrical cutting elementof device (50) is instead used to make a micro steam explosion to tearthe capsule, not burn it. In addition, the electrical cutting element ofdevice (50) completes the severing of the tissue to free the severedpiece from the capsule, unlike electrocautery devices that often onlyweaken the tissue and require tweezers to remove the severed piece.Further, in some embodiments, the electrical cutting element has a massof 0.35 milligrams or less, so bulky heating elements are not requiredas are commonly found with electrocautery instruments.

With the mechanical cutting element, the element has one or moreultrasharp microteeth (or other tissue-severing mechanism) that piercethe capsule as the force of suction pulls the membrane past the teeth(described below) to sever the circular patch. As explained above,mechanical knife devices used in the past for performing capsulotomiesuse the knife to stretch the tissue to provide enough force against thecutting edge. In contrast, in the present invention, the reaction forceneeded for cutting with the mechanical cutting element of device (50)comes from suction supplied by the device, not from trying to use thestiffness of the tissue by pushing against it. The suction pulls thetissue perpendicularly into the cutting edge, so there is no lateraldistortion away from where the cut is supposed to go, and precisionmicrocuts can be reproducibly made. In addition, a complete cut can bemade with the cutting element (60), as opposed to the multiple passesthat are frequently required with microknives used in the past. Thoughthe cutting element is a continuous ring in the embodiments of FIGS. 1and 2, this is not required. It could instead be a non-continuous ring,or could include discrete microteeth anchored in an elastomeric supportring.

The combined electro-mechanical cutting element has 1 microtooth (oroptionally, more than one) or other tissue severing mechanism thatproduces an initial tear in the capsule. The tear is propagated usingthe electrical cutting element design for applying a short electricalpulse, as explained above. The tear can be propagated to complete thecapsulotomy by a lower steam pressure than would be required for anintact capsule.

The stem (62) that extends from the suction cup (67) contains lumens(55, 65, 66) to transport liquids and gases. In some embodiments of thedevice, one or more of the lumens contain electrical conductors, such asthe electrical leads (54, 64) shown in FIG. 1. In the embodiment shown,the lumen (65) connects to the inner chamber (58) of the suction cup viaorifice (56). The central lumen (55) connects to the outer chamber (57)of the suction cup through orifice (52). For devices using electricalcutting elements, the electrical leads (54, 64) can be separated by aninsulator (63) located in lumen (55). The leads (54, 64) do not fill thelumen (55), but instead leave some free space for fluids to pass throughtoo. The electrical lead end (53), as it connects to the cutting element(60) in the outer chamber (57), is illustrated in FIG. 2. Lumen (66) isused for inflating and deflating the suction cup (67), which is relevantfor embodiments in which the suction cup is inflatable (described inmore detail with regard to later Figures).

One or more of the lumens (55, 65, 66) can also act as suction elementsthat connect to and provide suction to the suction cup (67). In oneembodiment, suction can be applied independently to the inner chamber(58) and to the outer chamber (57). For example, lumen (55) connectingthe outer chamber (57) can provide suction to that chamber, while lumen(65) connecting to the inner chamber 58 can provide suction to thatchamber. The functions of the different lumens (55, 65, 66) can differacross different embodiments of the device (50).

The suction applied to the suction cup (67) can serve a number ofpurposes. The suction can be used to secure the device (50) to thetissue for the cutting procedure. The suction can also provide a vacuumseal against the tissue. The suction can further pull portions of thetissue up into the suction cup (67) for securing the suction cup (67)against the tissue or for permitting severing of the tissue using thecutting element, as explained in more detail regarding FIGS. 4-9. Theapplied suction force can stretch the capsular membrane over the edge ofthe cutting element (60) to create a state of high tensile stressexactly on the circle where cutting is desired. Suction can also be usedto retain the cut portion of tissue inside the device (50) duringremoval. In one embodiment, suction is provided to the outer chamber(57) to create a seal against the tissue and to apply tension to theannular region of the lens capsule where a precise cut is to be made,and suction is applied independently to the inner chamber (58) to holdthe circular patch of tissue that is to be removed. Since the cuttingelement (60) is built-in directly to the device (50) that also providesthe suction and fluid flushing capabilities, the device (50) can be usedin a one-step procedure for performing a capsulotomy, rather thanrequiring a second step/device for flushing. In the embodimentillustrated in FIGS. 1 and 2, the lumens (55, 65, 66) each run alonginside the length of the stem (62). However, other configurations arealso possible. For example, the suction cup (67) could be connected toone or more tubes or other elements separate from the stem (62) thatprovide the same functions as lumens (55, 65, 66).

FIG. 3a shows the device during use in the eye (1), according to anembodiment of the invention. The parts of the eye (1) illustrated inFIG. 3a include the sclera (7), the cornea (2), the iris (6) and thelens capsule (5). In FIG. 3a , the surgeon has made an incision (3)through the cornea (2). In this embodiment, an insertion tube (4) isused to deliver the device (50) to the eye (1) and through the incision(3). However, other delivery mechanisms can be used too. The insertiontube (4) illustrated in FIG. 3a has been pushed through the incision (3)so that the suction cup (67) could be pushed out of the tube (4) andinto the anterior chamber of the eye (1).

The device (50) illustrated in FIG. 3a is being used by an ophthalmicsurgeon to perform a capsulotomy. That is one of the steps that istypically performed in cataract surgery. The capsule (5) is atransparent membrane that encapsulates the lens of the eye (1). For theoperation, the iris (6) is made to stay in its maximum open state toallow the rim of the suction cup (67) to pass through the pupil and makea tight seal between the underside (8) of the cup (67) and the lenscapsule (5). A circular hole is cut in the anterior capsule so that thecataractous lens can be removed, and the IOL can be inserted. In someembodiments, the circular opening in the capsule (5) or other tissue isapproximately 5.5 mm in diameter. However, other diameter openings canbe created with other embodiments, as desired for various surgicalprocedures (e.g., 1 mm, 5 mm, 10 mm, 20 mm, 100 mm, and so forth). The5.5 mm diameter circular patch of excised membrane is removed using thedevice (50) and can be discarded, but the rest of the capsular bagshould remain undamaged so that it will have the structural integrityneeded to hold the IOL.

FIG. 3b illustrates the deformable device (50) withdrawn inside theinsertion tube (4), according to an embodiment of the invention. Thedevice (50) can be pulled into the lumen of the insertion tube (4), andthe suction cup (67) can be collapsed to fit inside the tube (4). Thecross section of the insertion tube (4) can be elliptical to minimizethe vertical stretching of the corneal incision and deformation of thecutting element (60), though it can also be circular or take on othershapes.

Both the suction cup (67) and the cutting element (60) can be made frommaterials that can restore their circular shape after being pushed outof the insertion tube (4). As stated above, the suction cup (67) can bemade from an elastomer (such as the medical grade silicone MED-6015 fromNUSIL, INC.®), and the cutting element (67) can be made from a hardelastic material, such as spring steel or stainless steel. Though thecutting element (67) can also be made of other materials and metals.Typically, for electrical cutting elements, the material for the cuttingelement is electrically conductive, and for mechanical cutting elements,the material is hard enough to pierce the membrane.

For both electrical and mechanical cutting elements, the material isalso generally elastic enough to return to its prior shape after beingsqueezed to get through the corneal incision, or soft enough to bepushed back into circular shape by the polymeric support ring and/or bythe suction cup in which it is mounted. For example, for an electricalcutting element, the materials can include those made by photochemicaletching, such as spring steel, stainless steel, titanium nickel alloy,graphite, nitinol (NiTi alloy “memory metal”), nickel, nickel-chromealloy, tungsten, molybdenum, or any other material that will allow theelement (60) to return to its prior shape upon exit from the tube (4).Other materials for electrical cutting elements include electricallyconductive elastomers, including elastomers (e.g., silicone orpolyurethane) mixed with appropriately shaped conductive particles(e.g., silver, gold, graphite, copper, etc) that can establish contactwith each other and continue to be in contact with each other for theduration of the electrical discharge. An additional example of amaterial for electrical cutting elements includes a compliant mesh ofvery fine wires (e.g., diameter of about 1 or 2 microns) that can beanchored in the elastomeric support ring to make the conductive element.As a further example, materials can be used for electrical cuttingelements that are made by sputtering metal onto a polymeric support,such as high conductivity metals (e.g., gold, aluminum, copper, etc.),which can be used to make very thin (e.g., 1 micron) elements withresistance within the usable range (e.g., 1 to 10 ohms) deposited by RFplasma sputtering. As examples of materials used for mechanical cuttingelements, they can include photochemically etched metal (e.g., stainlesssteel), or a relatively hard plastic (e.g., phenolic), among others.Discrete micro teeth could be etched from single crystal silicon.Photochemical etching can used to make cutting elements that have athickness of, for example, 25 microns, or 12.5 microns, or 5 microns,and so forth.

In embodiments in which the suction cup (67) is inflatable, the cuttingelement (67) can be helped to return to its ring shape by the inflationof the cup (67). So, in inflatable embodiments, using a material for thecutting element (67) that has ability to return to the ring shape isless important. In embodiments in which the cutting element (60) is anelectrical cutting element, the element (60) is composed of a materialthat is electrically conductive, such as the metals described above.

The insertion tube (4) can be made of various different materials, suchas stainless steel or plastic. The insertion tube (4) can be designed tohave the lowest possible coefficient of friction, and can also belubricated to minimize the force needed to slide the suction cup in thetube. The entrance (4 a) to the insertion tube is shaped (e.g., beveled)in this embodiment to make it easier to pull the suction cup (67) intothe tube (4). The end of the insertion tube is also shaped to facilitateits penetration through the corneal incision. Note in FIG. 3a that thetube of elliptical cross section has been cut at a 45 degree angle (forexample) so that the initial entry into the incision is made by just thetip of the tube and with a very small cross section, so the force islow.

Surgical Procedure

FIGS. 4-9 schematically show the steps in the automated capsulotomyprocess, according to an embodiment. FIG. 4 illustrates an embodiment ofthe suction cup (67) in which the cup includes a roof (14) and an outerperimeter (11). In this embodiment, the suction cup (67) includes anouter chamber (12) and an inner chamber (15) separated by a wall (16).Mounted to this embodiment of the suction cup (67) is a cutting element(13) with an edge (10) for cutting tissue. The outer chamber (12) actsas an outer vacuum channel at the circular rim of the suction cup (67)that uses the force of suction to hold the device (50) onto the lenscapsule (50), and the device (50) has tubing (described regarding FIGS.1 and 2) that extends out through the cornea for access to otherapparati to provide independent fluid communication to the outer chamber(12) and to the inner chamber (15).

In FIG. 4, the surgeon has brought the suction cup (67) into contactwith the capsule (5) centered on the optical axis. The surgeon can thenpress a button, and the remaining steps that result in a severed tissuepatch can occur automatically under computer control. Suction is appliedto the inner chamber (15) of the suction cup (67). The suction providedto the inner chamber (15) creates a bulge (17) in the tissue, which isshown in FIG. 5. This bulge locks the capsule (5) in place, and sosecures the suction cup (67) against the capsule (5) so it will notslide relative to the capsule (5).

FIG. 6 illustrates the next step in which suction is applied to theouter chamber (12) of the suction cup (67). This produces annular bulges(18 b) and (18 c) in the capsule (5), stretching it over the edge (10)of the cutting element (13) to produce the maximum tensile stress in themembrane at location (18 a), which is the radius at which cutting isdesired. The diameter of the final hole might not be equal to thediameter of the cutting element (13) due to the fact that the cuttingoccurs when the lens is deformed and the capsule (5) is stretched.However, since the process is reproducible, it can be readily determinedwhat diameter hole results from any given diameter of cutting element(13), and adjustments to the cutting element design can be madeaccordingly.

If the cutting element (13) is a mechanical one, then it can include oneor more ultrasharp microteeth that will pierce the capsular membrane.The applied pressure due to the suction pulling the tissue against thecutting element will do the work of moving the cutter completely throughthe membrane to sever the circular patch. In embodiments in which thecutting element (13) is mechanical, the surgical method skips FIG. 7 andgoes directly to FIG. 8.

If the cutting element (13) is an electrical one, then it is essentiallya heating element (e.g., a resistor). The applied suction pressure willstretch the capsule (5) over the cutting (heating) element (13) tocreate a circle of high tensile stress, but not enough to tear themembrane. FIG. 7 shows the electrical element (13), and illustrates theinstant at which the electrical discharge occurs. The thin film of watertrapped between the heating/cutting element (13) and the capsule isheated (e.g., to 1000° C.) in a few microseconds. This becomes highpressure steam that expands and pushes the membrane away from theheating/cutting element (13). The force of suction (22, 23) is alreadypresent, acting to stretch the membrane. The additional stretchingforces (21, 24) from the expansion of the steam increases the tensilestress enough to create the desired tear (20) in the membraneinstantaneously all the way around the circular heating element (13).

Some prior devices require the surgeon to manually hold a cuttingelement against the capsule, pushing the lens down into the vitreous bya gross displacement until the equal and opposite reaction force can bedeveloped within the fibers of the easily damaged zonules which hold thelens in the eye. Reaction force is also generated in these other devicesby increasing the pressure within the vitreous to push back on the lens,but that pressure also pushes on the retina, and is risky. In contrast,with the device (50) described here, the capsule (5) is sucked againstthe cutting element (13), so the force and reaction force are both rightthere entirely contained within the device (50) and the capsule (5). Thedevice does not require pushing on other eye structures. Furthermore,uniform, intimate contact over the full 360 degrees of the ring isensured, unlike with prior, manual push devices, in which the surgeonnever knows if he has uniform contact (holding the device with even animperceptible tilt relative to the lens will cause non-uniform contactforce around the ring). With the device (50), since the pressure againstthe cutting element (13) is uniform, heat transfer will be uniform, andcutting will progress uniformly. In addition, as explained above, thedevice (50) applies less energy to the tissue for a shorter durationthan electrocautery instruments that burn the tissue by applying heatfor long durations.

FIG. 8 shows the completely severed circular patch (25), which wassevered using any of the types of cutting elements (13) described above.There is no mechanical attachment or adhesion between the capsule (5)and the lens. When the suction to the outer chamber (12) is turned off,fluid can then be injected into the outer chamber (12) as the device(50) is lifted away from the lens. During removal of the device (50)from the location of the surgery, the severed patch of membrane in theinner chamber (15) is carried away in the device since a suction forceis maintained there in the inner chamber (15). This leaves the remainder(26) of the capsule (5) behind, as desired.

In summary, as explained above, the suction applied in device (50) canbe used to do four things (among others): (a) to provide a clampingforce to hold the device to the lens capsule, (b) to stretch the capsulemembrane over the cutting element (13) and develop significant tensilestress within the membrane where cutting is desired, (c) to retain thesevered patch (35) of membrane within the inner chamber (15) for removalfrom the eye, and (d) after cutting, to push the device (50) away fromthe lens by turning off the suction in the outer chamber (12) andinjecting liquid (most likely, that which was just sucked into the tubepreviously) into the outer chamber (12). In addition, the device willfunction even if there is some leakage, because it is not necessary toisolate fluids as long as the leakage is small enough that the suctionflow can maintain the pressure needed to provide the required forces.Thus, the device (50) provides all of these features (e.g., suction,cutting element, etc.) on the scale of the tissue size that the surgeonis attempting to cut. Once the surgeon presses the button, as explainedabove, the device can typically be removed from the eye (along with thesevered piece of tissue) within a few seconds (e.g., 1 second, 2seconds, 5 seconds, 10 seconds, 20 seconds, 50 seconds, 1 minutes, andso forth).

Cutting Element Designs

FIGS. 10-11 show a schematic cross section of an electrical cuttingelement (37), according to an embodiment. In this design, the sides ofthe element (37) have a nonconducting layer (36) (e.g., plastic oranother nonconducting material). With this layer (36), the heat of theelement (37) is focused at the edge (38) of the element (37). Thus, thesteam will be produced only at the edge (38) to stretch the membrane atthe bend (39) of the tissue and create the cut (40), which is shown inFIG. 11.

FIG. 12 shows a schematic cross section of an electrical cuttingelement, according to an embodiment. In this design, the elementincludes a lumen that is constructed to allow a greater volume oftrapped water (42) and a greater surface area of contact between thewater and the sides of the element (41, 43, 44). When discharged, thiswill create a directed jet of steam to cut the membrane at (45).

FIGS. 13-14 show in schematic cross section of an electrical cuttingelement (30), according to an embodiment. This element (30) creates acut (34) in the side of the bulge (33) of tissue, as the element (30) ispositioned over to the side of the device (50). Other designs are alsopossible, in which the cutting element is positioned differently in thesuction cup and/or the tissue is cut at other locations.

Other Embodiments of the Microsurgery/Capsulotomy Device

FIGS. 15-16 show an exploded view of a device, according to anembodiment. The device in this design has a suction cup (67), a cuttingelement support ring (70), and an electrical cutting element (60) withtabs (71) that anchor it to the support ring (70). Grooves (75) in thesides of the support ring (70) ensure the distribution of suctionthroughout the outer chamber. Leads (53, 76) connect to the ends of thewires (54, 64) which are separated by insulator (63). There is a smallgap (77) so that the electrical current is forced to go all the wayaround the ring (70). The gap is small enough that the steam bubbleproduced during discharge is big enough to continue the tear in themembrane past the gap (77).

FIG. 17 shows, in partial cross section, an inflatable/deflatablesuction cup design using a skin and web construction, according to anembodiment. This can be molded using the “lost wax” method, which isknown to those of ordinary skill in the art. FIG. 18 shows the wax core(96) that would be placed in the mold to produce the structure in FIG.17.

FIG. 19 shows, in cross section, an inflatable/deflatable suction cupdesign, according to an embodiment. The suction cup design has a skin(101) enclosing a space that would be filled with an open cell foam(such as a polyurethane foam). The fibrils that comprise the foam arebonded to the skin (101), and span the empty space so the suction cupwill maintain its shape when it is pressurized with a fluid (e.g., withsaline solution). When the space within the foam is evacuated, thesuction cup collapses to a small cross section under the pressure of thesurrounding atmosphere.

FIG. 20 shows an inflatable/deflatable suction cup design, according toan embodiment. This design uses simpler geometric elements (e.g.,circular cross-section tubes) that do not need any internal webs or opencell foam to keep their shape under pressure. Port (112) provides forsuction to the inner chamber. Port (114) provides for suction to theouter chamber. Ports (113, 115) will connect to the same tube whichsupplies fluid (e.g., water or air) to inflate or deflate the structure.The cutting element support ring (70) can be attached to the suction cupby a very small amount of glue (such as clear silicone II RTV sealant,from GE®). The cutting element (60) can be over-molded by the supportring, or can be glued to it.

FIG. 21 shows a mechanical cutting element (120) with ultrasharpmicroteeth (121), according to an embodiment. This embodiment includestwo hundred of the teeth, though the number can vary with differentdesigns. FIG. 22 shows a close-up view of a few teeth, according to anembodiment. The teeth can be made by photoetching sheet metal, such as12.5 micron thick stainless steel, from one side and stopping the etchshortly after it breaks through to the other side.

FIG. 23 shows an electromechanical cutting element having one tooth(130), according to an embodiment. As in all the other embodiments, thecapsule does not contact the cutting element until after the suction hasbeen turned on for the outer chamber (which does not occur until aftersuction has already been applied in the inner chamber). The capsule isanchored by the inner chamber, so it does not shift position as suctionbuilds up in the outer chamber. It simply develops a bulge that extendsinto the depth of the outer chamber, and the cutting element contactsthe membrane in a perpendicular manner. In this case, the tooth contactsthe membrane, and punctures it. That starts a tear which can becompleted by the pulse of steam that will be generated by the electricaldischarge.

FIG. 24 shows a close-up view of the electrical connections to theelectrical cutting element, according to an embodiment. The electricalcutting element (60) is mechanically held by the plastic support ring(70) that may be molded over it (enclosing tabs 71) or glued to tabs(71) (ring 70 is in turn glued into the suction cup). The electricalcutting element is spot welded (e.g., by e-beam or laser welding) toleads (53, 76) which in turn are spot welded to pins (153, 176), whichare mechanically pressed into holes in wires (54, 64), which aremechanically held together by insulation (63) (which may be epoxy).

Disposable Unit

FIGS. 25-27 show the entire disposable unit (200) and FIG. 28 shows thedisposable unit (200) attached to the handpiece (252), according to anembodiment. FIGS. 25-27 illustrate the housing (251) of the unit (200),the insertion tube (212) that is incorporated into the unit (200)design, the stem/arm (62), the suction cup (67), and the underside ofthe suction cup (67) that includes a cutting element (60). The suctioncup (67), stem (62), and cutting element (60) were described in detailabove. The housing (251) is typically composed of plastic, though it canalternatively be composed of other materials (e.g., metal, etc.).

FIG. 25 illustrates a rear view the unit (200) of themicrosurgery/capsulotomy device including a back view of some of theinternal components of the unit (200). In FIG. 26, the housing (251) isremoved to show the internal components. The insertion tube (212) is anintegral part of the housing (251) so it has also been removed in FIG.26 to show the underlying internal features. The disposable unitprovides a closed sterile system that does not introduce anycontamination to the patient or transmit any contamination from thepatient to the reusable handpiece (252), which is shown in FIG. 28.FIGS. 25 and 26 illustrate bellows (206, 208) inside the unit. Any fluidremoved from the patient (e.g., fluid from inside the eye) will betrapped in these bellows (206, 208). Fluid flow is produced by pushingor pulling on closed bellows (206, 208, and 210). In some embodiments,the bellows (206, 208, and 210) are composed of plastic, though othermaterials can also be used (e.g., elastomeric materials, flexiblemetals, etc.).

To use the unit, the surgeon will grip the housing (251) and plug itinto a non-disposable (reusable) handpiece (252) (FIG. 28) such that theconical mechanical connectors (203, 228, 230) engage latching grippers(not shown). The grippers can be moved by electric motors during theoperation as needed to compress or expand the bellows. Bellows (206) hasfluidic communication with the outer chamber of the suction cup, bellows(208) connects to the inner chamber of the suction cup, and bellows(210) connects to the inflatable space (for inflatable suction cups).All fluidic connections can be made in the manifold (235) at thefactory. All components can be mounted on the circuit board (211), andthis circuit board ensemble can be moved as a unit with respect to thehousing so that the suction cup can be pulled into the insertion tube(212), and pushed out of the insertion tube (212). In addition to thelatching gripper mechanical connections, there are electrical contactsin the reusable part of the handpiece (252) that connect to electricalleads (201) and (202) on the circuit board (211) (for units having anelectrical cutting element).

FIGS. 25-27 illustrate an example of a disposable unit for use with theinvention. However, other unit designs can also be used. In someembodiments, the unit is a more simple structure, some or all of theinternal components, bellows, etc. exist separate from the rest of thedevice. In the embodiment described above, the insertion tube (212) canalso be a separate structure.

Referring now to FIGS. 29a and b , the procedure for use of the unit 200in a microsurgery/capsulotomy procedure is shown, according to anembodiment. The procedure includes opening the sterile packagecontaining the disposable unit (200). It is stored in the extendedposition with the suction cup (67) outside the insertion tube (212) toensure that the elastomer does not take a set. The unit is plugged (400)into a reusable handpiece (252), as described above and as illustratedin FIG. 28. Bellows (206) and (208) are then fully compressed (402) totheir minimum volume. For an inflatable-type suction cup, the inflatingliquid is sealed into the suction cup/bellows (210) system at thefactory. So, optionally, the surgeon can expand (403) the bellows tomake the suction cup deflate in an inflatable embodiment. The surgeoncan next pull/withdraw (404) the suction cup (67) into insertion tube(212) by a motor that moves the entire circuit board ensemble backrelative to housing (251). The surgeon then inserts (406) the insertiontube tip into a corneal incision created by the surgeon. The circuitboard ensemble is moved forward relative to the housing (251) to push(408) the suction cup (67) out. The friction in the insertion tube (212)should be kept as low as possible (e.g., by choice of materials andlubrication). Optionally, bellows (210) is compressed (409) by anelectric motor to inflate the suction cup (if it is an inflatable type).The surgeon moves (410) the device to the lens capsule, centers the ringover the optic axis of the lens, and brings it into contact with thelens capsule.

In one embodiment, the surgeon presses (412) a button that executes therest of the capsulotomy operation automatically under the control of anembedded microcontroller in the handpiece (252). The controller turns onthe electric motor that expands (414) bellows (208) to produce suctionin the inner chamber of the suction cup. The suction pulls tissue intothe inner chamber to secure the suction cup in place. The suctionpressure can be measured by the motor current, and the fluid flow intothe bellows can be measured by the rotational position of the motorshaft as a function of time. When the controller determines that thedesired suction pressure and a sufficiently leak tight seal have beenachieved, it will turn on the electric motor that expands (416) bellows(206), which applies suction to the outer chamber of the suction cup(67).

Moving on to FIG. 29b , this Figure shows a continuation of theprocedure of 29 a. The suction pulls tissue into the outer chamber forcutting (418) the tissue. Once it is determined that the desired suctionpressure has been achieved in the outer chamber, then either anelectrical discharge occurs to cut (418) the tissue (for the electricalcutting element type), or the cut (418) will be finished mechanically(for the mechanical cutting element type). Then, bellows (206) iscompressed (420) to release suction to the outer chamber and to pushfluid into the outer chamber to push the lens away from the suction cup(67). Suction in the inner chamber is reduced (422) until there is justenough to retain the cut patch of membrane there. Optionally, bellows(210) is expanded (423) (for inflatable suction cups) to deflate thesuction cup (67) (for inflatable suction cup). The suction cup (67) andthe cut patch of membrane are pulled (424) into insertion tube (212) andthe insertion tube (212) is pulled out of/removed (426) from the cornealincision. The disposable unit is pulled off of/removed from (428) thereusable handpiece (252) and thrown away.

The reusable handpiece (252) can take on a variety of forms, and FIG. 28illustrates just one example. In one embodiment, the handpiece (252) isa battery powered unit having an embedded microcontroller, a reversibleelectric motor for each bellows, and an electric motor to move thecircuit board ensemble. For electrical cutting elements, the handpiece(252) will contain a capacitor.

Although bellows (206) and (208) can accommodate only a limited volumeof total flow, it is far more than needed to do the job. The volume ofthe bellows can be, for example, 10 milliliters when fully expanded,while the total fluid sucked from the eye should be less than 1 ml.Normally there will be another fluidic line inserted into the eye toinject or withdraw fluid as needed to maintain the correct internalvolume of the anterior chamber throughout the course of the operation.It is possible to incorporate such a make-up line into the device of theinvention, if desired.

As noted above, the devices and procedures described in this applicationcan be used in performing lens capsule surgery (e.g., for cataracttreatment, for implantation of an IOL, or other treatments in whichcreation of an opening in the lens capsule is desired). As explainedabove, the devices and procedures described here are not limited to lenscapsule surgery, but can also be useful in other treatments of the eye,such as a corneal surgery, treatments for glaucoma, microfinestration ofthe optic nerve, surgeries involving decemet's membrane, among others.In these types of applications, the procedures and devices function ingenerally the same manner as described above regarding the lens capsulesurgery. In addition, the devices and procedures may be useful forperforming other medical procedures outside of the eye, such asprocedures involving fenestration of brain dura, and others. In thesetypes of applications, the procedures and devices function in generallyin the same manner as described above regarding the lens capsulesurgery. The devices for these surgeries might look a bit differentbecause they have to fit into differently-shaped organs, but the cuttingmechanism would use the same ideas.

Examples

A number of prototype designs were built and tested on lenses fromrabbit eyes. The cutting elements were made by photochemical etching 302stainless steel full hardness sheet foil 25 microns thick. The isotropicetching was done from one side to produce a beveled edge as indicated inFIG. 22. Capsulotomies were successfully performed with electricalcutting elements having cross sections of 25 microns×50 microns, andresistances of 4 to 6 ohms, with the electrical discharge from a 90microfarad foil capacitor with initial voltage of 70 V and final voltageof 0 V. The cutting element was observed to flash a bright yellow color,which corresponds to a temperature of about 1000° C. Successful suctioncups were molded from silicone MED-6015, MED4-4220 (from NUSIL, INC.®),and from TAP silicone RTV (from TAP PLASTICS®). The discharge times wereless than 1 millisecond. Shorter discharge times could be achieved byincreasing the initial voltage (e.g., 400 V), and/or decreasing thecutting element resistance (e.g., 1-2 ohms). The total energy needed toheat the steel cutting element and the trapped layer of water was about0.2 joules. This amount of energy would be released from a 90 microfaradcapacitor going from 400V to 394V. This corresponds to a 3% discharge,so only a small fraction of the RC time constant is needed. One way tostop the discharge at this point is to design the cutting element tomelt and break the circuit upon dissipating the desired quantity ofenergy. Another way is to use an electronic control circuit. A dischargeof 0.2 joules in 10 microseconds corresponds to a power of 20 kW. Thetotal amount of energy is too small to damage the surrounding tissue asthe heat is conducted away over the next several milliseconds.

Prototype mechanical cutting elements were also made by one-sidedphotochemical etching of stainless steel full hard foil 25 micronsthick. The largest number of teeth tried was 72, and this madesuccessful capsulotomies in rabbit eye lenses when a suction of 7 inchesof mercury, or more, was applied to the silicone suction cup.

The above description is included to illustrate the operation of theembodiments and is not meant to limit the scope of the invention. Thescope of the invention is to be limited only by the following claims.From the above discussion, many variations will be apparent to oneskilled in the relevant art that would yet be encompassed by the spiritand scope of the invention. As used herein any reference to “oneembodiment” or “an embodiment” means that a particular element, feature,structure, or characteristic described in connection with the embodimentis included in at least one embodiment. The appearances of the phrase“in one embodiment” in various places in the specification are notnecessarily all referring to the same embodiment.

1. A surgical device for excising a corneal tissue of an eye, the device comprising: a cutting element including an annular ring shape with a cross section having an inner edge and an outer edge, wherein the cutting element is collapsible for insertion through an incision in a tissue layer to access the tissue for excision, and wherein the cutting element is configured to return to the annular ring shape after the insertion through the incision, the cutting element forming a circular enclosed interior space within the cutting element and configured to contain the excised tissue; two electrical leads attached to the cutting element such that, when an electrical pulse is applied, the electrical pulse is capable of traveling around the entire annular ring shape of the cutting element and is exposed only at a bottom surface of the cutting element; and an arm attached to the cutting element and configured for manipulating the cutting element.
 2. The device of claim 1, wherein the two electrical leads are disposed within the arm.
 3. The device of claim 1, wherein the two electrical leads are connected to the electrical cutting element on two different sides of an insulating gap in the cutting element such that, when an electrical pulse is applied, the electrical pulse is capable of traveling from a first of the two electrical leads around the entire annular ring shape of the cutting element to a second of the two electrical leads to excise the tissue.
 4. The device of claim 3, wherein the two electrical leads are adjacent to each other where the two electrical leads are connected to the cutting element.
 5. The device of claim 1, further comprising a polymeric support, wherein the cutting element comprises metal sputtered onto the polymeric support.
 6. The device of claim 1, wherein the cutting element is collapsible to a size that permits insertion through the incision in the tissue layer, the incision having a length of less than 3.0 mm.
 7. The device of claim 7, wherein the cutting element has a diameter between 4.5 mm and 7 mm.
 8. The device of claim 1, wherein the cutting element has an axial height of less than 1.5 mm.
 9. The device of claim 1, wherein an axial height of the cutting element from a bottom edge to a top edge of the cutting element exceeds a thickness of the cutting element from the inner edge to the outer edge of the cutting element.
 10. The device of claim 1, further comprising a nonconducting layer on at least one of the inner edge and the outer edge of the cutting element, the nonconducting layer configured to focus heat at the bottom surface of the cutting element.
 11. A surgical device for excising tissue of an eye, the device comprising: a cutting element including an annular ring shape, wherein the cutting element is collapsible for insertion through an incision in a tissue layer to access a tissue for excision, and wherein the cutting element is configured to return to the annular ring shape after the insertion through the incision, the cutting element forming a circular enclosed interior space within the cutting element and configured to contain the excised tissue; two electrical leads attached to the cutting element such that, when an electrical pulse is applied, the electrical pulse is capable of traveling around the entire annular ring shape of the cutting element; and an arm attached to the cutting element and configured for manipulating the cutting element.
 12. The device of claim 11, wherein the annular ring shape is configured to create a circular opening in the lens capsule.
 13. The device of claim 12, wherein the two electrical leads that are disposed within the arm.
 14. The device of claim 11, further comprising a nonconducting layer on a surface of the cutting element, the nonconducting layer configured to focus heat at a bottom edge of the cutting element, the heat generated by an electrical pulse.
 15. The device of claim 11, wherein the cutting element is collapsible to a size that permits insertion through the incision in the cornea having a length of less than 3.0 mm.
 16. The device of claim 11, wherein the cutting element has a diameter between 4.5 mm and 7 mm.
 17. The device of claim 11, wherein the height of the annular ring shape is less than 1.5 mm.
 18. The device of claim 11, wherein the thickness of the annular ring shape is about 25 microns.
 19. The device of claim 11, further comprising an insertion tube configured to contain the cutting element, wherein the device is configured such that the cutting element is collapsible before retraction into the insertion tube.
 20. The device of claim 11, wherein the cutting element comprises metal sputtered onto a polymeric support, the polymeric support being a suction cup mounted to the cutting element. 